US20150039071A1 - Fixation for implantable medical devices - Google Patents
Fixation for implantable medical devices Download PDFInfo
- Publication number
- US20150039071A1 US20150039071A1 US13/955,674 US201313955674A US2015039071A1 US 20150039071 A1 US20150039071 A1 US 20150039071A1 US 201313955674 A US201313955674 A US 201313955674A US 2015039071 A1 US2015039071 A1 US 2015039071A1
- Authority
- US
- United States
- Prior art keywords
- distal
- segment
- approximately
- tine
- component
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Granted
Links
Images
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N1/00—Electrotherapy; Circuits therefor
- A61N1/02—Details
- A61N1/04—Electrodes
- A61N1/05—Electrodes for implantation or insertion into the body, e.g. heart electrode
- A61N1/056—Transvascular endocardial electrode systems
- A61N1/057—Anchoring means; Means for fixing the head inside the heart
- A61N1/0573—Anchoring means; Means for fixing the head inside the heart chacterised by means penetrating the heart tissue, e.g. helix needle or hook
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N1/00—Electrotherapy; Circuits therefor
- A61N1/18—Applying electric currents by contact electrodes
- A61N1/32—Applying electric currents by contact electrodes alternating or intermittent currents
- A61N1/36—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation
- A61N1/362—Heart stimulators
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N1/00—Electrotherapy; Circuits therefor
- A61N1/18—Applying electric currents by contact electrodes
- A61N1/32—Applying electric currents by contact electrodes alternating or intermittent currents
- A61N1/36—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation
- A61N1/372—Arrangements in connection with the implantation of stimulators
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N1/00—Electrotherapy; Circuits therefor
- A61N1/02—Details
- A61N1/04—Electrodes
- A61N1/05—Electrodes for implantation or insertion into the body, e.g. heart electrode
- A61N1/056—Transvascular endocardial electrode systems
- A61N1/057—Anchoring means; Means for fixing the head inside the heart
- A61N2001/0578—Anchoring means; Means for fixing the head inside the heart having means for removal or extraction
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N1/00—Electrotherapy; Circuits therefor
- A61N1/02—Details
- A61N1/04—Electrodes
- A61N1/05—Electrodes for implantation or insertion into the body, e.g. heart electrode
- A61N1/056—Transvascular endocardial electrode systems
- A61N1/057—Anchoring means; Means for fixing the head inside the heart
- A61N2001/058—Fixing tools
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N1/00—Electrotherapy; Circuits therefor
- A61N1/02—Details
- A61N1/04—Electrodes
- A61N1/05—Electrodes for implantation or insertion into the body, e.g. heart electrode
- A61N1/056—Transvascular endocardial electrode systems
- A61N2001/0585—Coronary sinus electrodes
Definitions
- the present invention pertains to implantable medical devices, and, more specifically, to tissue-penetrating fixation components thereof.
- An implantable medical device for the delivery of stimulation therapy and/or for diagnostic sensing, may include at least one tissue-penetrating fixation component configured to hold the device at an implant location.
- FIG. 1 is a schematic diagram that shows potential cardiac implant sites for such a device, for example, within an appendage 102 of a right atrium RA, within a coronary vein CV (via a coronary sinus ostium CSOS), or in proximity to an apex 103 of a right ventricle RV.
- FIG. 2 is a plan view of an exemplary implantable medical device 200 , which includes a tissue-penetrating fixation component formed by a plurality of tine portions 230 .
- device 200 including a hermitically sealed housing 220 that contains control electronics and a power source (not shown), and which defines a longitudinal axis 2 of device 200 .
- Housing 220 may be formed from a medical grade stainless steel or titanium alloy and have an insulative layer formed thereover, for example, parylene, polyimide, or urethane.
- device 200 includes a pair of electrodes 261 , 262 , which may form a bipolar pair for cardiac pacing and sensing; tine portions 230 surround electrode 261 and are configured to penetrate tissue in order to hold electrode 261 in intimate contact with tissue, for example, at one of the aforementioned implant sites, while securing, or fixating device 200 for chronic implantation at the site. Further description of a suitable construction for device 200 may be found in the co-pending and commonly assigned United States patent application having the pre-grant publication number 2012/0172690 A1.
- device 200 may be delivered to an implant location via a delivery catheter 300 .
- a delivery catheter 300 For example, with reference to FIG. 1 , if the target implant site is located in the right atrium RA, coronary vein CV, or right ventricle RV, a distal end 310 of catheter 300 may be maneuvered into the heart through a superior vena cava SVC or an inferior vena cava IVC, according to a transvenous delivery method known in the art.
- FIG. 3A shows a partial cross-section of distal end 310 of catheter 300 , which is formed like a cup to hold and contain device 200 for delivery to the implant site.
- FIG. 1 shows a partial cross-section of distal end 310 of catheter 300 , which is formed like a cup to hold and contain device 200 for delivery to the implant site.
- FIG. 3A illustrates device 200 having been loaded into distal end 310 so that a hook segment 231 of each tine portion 230 is elastically deformed, from a pre-set curvature thereof, to an open position, at which a distal segment 232 of each tine portion 230 extends distally toward an opening 313 of catheter distal end 310 .
- Each tine portion 230 is preferably formed from a superelastic material, such as Nitinol.
- FIG. 3A further illustrates a deployment element 320 abutting a proximal end of device 200 and extending proximally therefrom, through a lumen of catheter 300 , and out from a proximal opening 301 thereof.
- Element 320 may be moved, per arrow M, by an operator to push device 200 , per arrow P, out from opening 313 of distal end 310 , for example, when opening 313 has been located by the operator in close proximity to tissue at the target implant site.
- FIG. 3B is an enlarged view of distal segment 232 of one of tine portions 230 , wherein a tissue-piercing tip 322 , which terminates distal segment 232 , has just been pushed out through opening 313 of distal end 310 of catheter 300 and into contact with tissue T.
- FIG. 3B illustrates distal segment 232 supported by the surrounding wall of distal end 310 , in proximity to opening 313 , so that the push force of deployment element 320 is effectively transferred through tip 322 to first compress the tissue T, as shown, and then to pierce the tissue T for penetration therein, which is shown in FIGS. 3C-D .
- FIGS. 3C-D FIGS.
- tine portions 230 illustrate partial tine penetration and full tine penetration, respectively, as deployment element 320 continues to push device 200 out opening 313 . It can be seen that the elastic nature of each tine portion 230 , once the constraint of the distal end 310 is withdrawn, allows the corresponding hook segment 231 to relax back toward the pre-set curvature thereof within the tissue.
- the full penetration of tine portions 230 shown FIG. 3D , is representative of acute fixation of device 200 at the implant site, for example, for the evaluation of device performance (e.g., pacing and sensing via electrodes 261 , 262 ). It should be noted that, at some implant sites, tine portions 230 may, at full penetration, extend back out from tissue T, for example, generally toward distal end 310 of catheter 300 .
- a tether 350 is shown looping through an eye feature 205 formed at the proximal end of device 200 ; tether 350 extends proximally through a lumen of deployment element 320 to a proximal end 351 thereof, outside a proximal end of deployment element 320 , which may be seen in FIG. 3A .
- the operator may use tether 350 to pull device 200 back into distal end 310 , thereby withdrawing tine portions 230 from the tissue, so that device may be moved by delivery catheter 300 to another potential implant site.
- proximal end 351 of tether 350 may be severed to pull tether 350 out from eye feature 205 of device 200 , and the fully penetrated tine portions 230 continue to fixate device 200 for chronic implant.
- a fixation component having tine portions similar to tine portions 230 , wherein the tine portions exhibit a suitable baseline performance, for example, in terms of a deployment force, an acute retraction force (for repositioning), atraumatic retraction, and acute and chronic fixation forces. Yet, there is still a need for new configurations of tine portions for implantable devices, like device 200 , that may further enhance fixation.
- Embodiments of the present invention encompass implantable medical devices (e.g., cardiac pacemakers) and tissue-penetrating fixation components thereof, which include one or more tine portions that are configured to mitigate the risk of compressing, for example, to the point of occlusion, blood vessels in proximity to the implant site, and to reduce the risk of tissue trauma during the retraction thereof from the tissue, for example, for repositioning.
- the tine portions may also be configured for increased strain relief during the flexing thereof, either at initial implant (particularly in cases where the retraction of penetrated tines is necessary for repositioning the device), or when subject to cyclic loading during a chronic implant of the fixated device, for example, within a beating heart.
- a tine portion of a tissue-penetrating component of an implantable medical device includes a hook segment and a relatively short distal segment, wherein the distal segment includes a tooth and an end that surrounds the tooth.
- the hook segment is elastically deformable from a pre-set curvature thereof to an open position, and the distal segment is pre-set to extend from a distal end of the hook segment along a relatively straight line that is approximately tangent to the distal end.
- the end of the distal segment includes a pair of legs and a distal arch, wherein the legs extend along a length of the tooth, on opposing sides thereof, and the distal arch extends between the legs and distal to a tissue-piercing tip of the tooth.
- the legs of the end are configured to bend in elastic deformation, when the hook segment is elastically deformed to the open position and a force is applied to push the distal arch of the distal segment against tissue, for initial tissue penetration, so that the bending of the legs expose the tip of the tooth to the tissue.
- the tissue-penetrating component further includes a base portion, for example, in the form of a ring, that is configured to be fixedly attached to the implantable medical device, wherein the tine portion may be one of a plurality of tine portions integrally formed with the base portion.
- each tine portion has a substantially constant thickness along an entire length thereof, from a proximal end of the hook segment to the distal arch of the end of the distal segment. Strain relief of each tine portion may be provided by a tapering of the hook segment thereof, from a first width thereof, in proximity to the proximal end thereof, to a second, smaller width thereof, in proximity to a distal end thereof. And, in some of the tapering embodiments, a width of distal segment, defined by the pair of legs thereof, is greater than the second width of the hook segment.
- FIG. 1 is a schematic diagram showing potential implant sites for embodiments of the present invention
- FIG. 2 is a plan view of an exemplary implantable medical device
- FIG. 3A is a plan view of the medical device loaded in a delivery catheter, according to some embodiments, wherein tine portions of a tissue-penetrating fixation component thereof are elastically deformed into an open position;
- FIG. 3B is an enlarged detail view of one of the tine portions initially contacting tissue at an implant site
- FIGS. 3C-D are plan views of the device and catheter in subsequent steps of implanting the device, when the tine portions have penetrated the tissue;
- FIG. 4A is a schematic representation of a flexing tine portion
- FIG. 4B is a perspective view of a tapered tine portion, according to some embodiments of the present invention.
- FIG. 6A is a plan view of an implantable medical device, according to some embodiments of the present invention.
- FIG. 6B is a perspective view of a tissue-penetrating fixation component, according to some embodiments of the present invention, separated from the device of FIG. 6A ;
- FIG. 6C is an elevation view of the component of FIG. 7B , according to some embodiments.
- FIG. 6D is a plan view of a tine portion of the component of FIG. 7B , according to some embodiments.
- FIG. 7A is an elevation view of a tissue-penetrating fixation component, according to some alternate embodiments, which may be incorporated in the device of FIG. 6A ;
- FIG. 7B is an estimated penetration path and an ‘as set’ relaxation plot for a tine portion of the component shown in FIG. 7A ;
- FIGS. 8A-B are plan views of tine portions, according to some alternate embodiments.
- FIGS. 9A-D are profiles and corresponding estimated penetration path and ‘as set’ relaxation plots of various tine portions, according to additional embodiments.
- FIG. 10A is a plan view of an implantable medical device, according to some alternate embodiments of the present invention.
- FIG. 10B is a perspective view of a tissue-penetrating fixation component, according to some embodiments, separated from the device of FIG. 10A ;
- FIG. 10C is an enlarged detail view of a distal segment of one of the tine portions of the FIG. 10B component initially contacting tissue at an implant site;
- FIG. 11A is an elevation view of a tissue-penetrating fixation component, according to yet further embodiments of the present invention, which may be incorporated in the exemplary device of FIG. 10A ;
- FIG. 11B is a plan view of a tine portion of the component of FIG. 11A , according to some embodiments.
- FIG. 4A is a schematic representation of one of tine portions 230 isolated from the above-described implantable medical device 200 , wherein an exemplary flexing, per arrow F, of tine portion 230 is illustrated.
- Such flexing may be encountered by tine portion 230 , once tine portion 230 has penetrated tissue to fix device 200 at a chronic implant site for cardiac monitoring and/or therapy, for example, as illustrated in FIG. 3D .
- fatigue life is a consideration influencing the configuration of tine portions for those implantable medical devices that may be subjected to cyclic loading caused by hundreds of millions of heart beats, over the life of their implant.
- FIG. 4A is a schematic representation of one of tine portions 230 isolated from the above-described implantable medical device 200 , wherein an exemplary flexing, per arrow F, of tine portion 230 is illustrated.
- Such flexing may be encountered by tine portion 230 , once tine portion 230 has penetrated tissue to fix device 200 at a chronic implant site for cardiac monitoring and/or therapy, for
- zone SC for example, in response to the flexing per arrow F, is circled; zone SC is located in proximity to a proximal end 31 of hook segment 231 of tine portion 230 , where hook segment 231 joins with a base portion 203 .
- Base portion 203 and tine portion 230 may be integrally formed, wherein base portion 203 is configured to be fixedly attached to device 200 . Stress concentration in zone SC may also result from deformation of hook segment 231 into the open position ( FIG.
- tine portions 230 effectively reduce the concentration of stress, as previously described in the aforementioned commonly-assigned U.S. patent application '690, some embodiments of the present invention incorporate tine portions that have tapered hook segments to further address the stress concentration, for example, as illustrated in FIG. 4B .
- FIG. 4B is a perspective view of a tine portion 430 , according to some embodiments, one or more of which may be integrated into device 200 , as substitute for tine portions 230 .
- a base portion 403 is shown integrally formed with tine portion 430 , according to some preferred embodiments, wherein base portion 403 is configured for attachment to a medical device, such as device 200 .
- FIG. 4B is a perspective view of a tine portion 430 , according to some embodiments, one or more of which may be integrated into device 200 , as substitute for tine portions 230 .
- a base portion 403 is shown integrally formed with tine portion 430 , according to some preferred embodiments, wherein base portion 403 is configured for attachment to a medical device, such as device 200 .
- FIG. 4B illustrates a hook segment 431 of tine portion 430 extending from a first end 41 thereof, in proximity to base portion 403 , to a second end 42 thereof, in proximity to a distal segment 432 of tine portion 430 , wherein hook segment 431 tapers from a first width W1, in proximity to proximal end 41 , to a smaller, second width W2, in proximity to a distal end 42 of hook segment 431 .
- the tapering of hook segment 431 provides strain relief during the aforementioned deformation/flexing, to alleviate the aforementioned stress concentration.
- FIG. 4B further illustrates an optional slot 48 (dashed lines), which may be formed through a thickness t of tine portion 430 , and extend between first width W1 and second width W2.
- slot 48 provides an additional means for providing strain relief, for example, when a limit on how narrow second width W2 may be, for example, no smaller than approximately 0.020-0.025 inch, so that distal segment 432 does not tear tissue upon retraction therefrom.
- optional slot 48 may include internal shear tabs (not shown) to help distribute out of plane loads, for example, orthogonal to the illustrated direction of flexing, per arrow F of FIG. 4A .
- distal segment 432 of tine portion 430 is shown having a shorter length than distal segment 232 of tine portion 230 , for example, to provide more flexibility in selecting a suitable implant site without risking undue trauma to tissue, upon penetration of tine portion 430 at the selected site.
- the shorter length can help to prevent perforation through the wall of a structure, for example, the heart, at some implant locations, and can reduce a probability for penetrated tine portions 430 to interfere with blood vessels, which interference, for example, may compromise coronary blood supply, as will be described below in conjunction with FIG. 5 .
- FIG. 5 is an estimated tissue penetration path and an ‘as set’ relaxation plot for tine portion 230 of device 200 ( FIG. 2 ), wherein tine portion 230 is formed from approximately 0.005 inch thick Nitinol.
- FIG. 5 includes a solid line, which represents the profile of tine portion 230 when device 200 is loaded in distal end 310 of catheter 300 ( FIG. 3A ) with hook segment 231 deformed to the open position.
- the origin, or zero coordinate, along the ordinate axis generally corresponds to the constraining wall of distal segment 310 of delivery catheter 300 .
- FIG. 5 is made up of a segmented line connecting circles, which corresponds to the estimated penetration path of tine portion 230 , for example, when device 200 is pushed out from distal end 310 and into tissue T ( FIGS. 3B-D ), and a dashed line, which represents the profile of tine portion 230 , according to the pre-set curvature, toward which the penetrated tine portion 230 relaxes over time.
- the volume of tissue between the segmented line and the dashed line approaches that which is squeezed or compressed by the penetrated tine portion 230 as it relaxes over time; the greater this volume, the greater the probability for the penetrated tine to compress or pinch one or more blood vessels that perfuse the tissue.
- FIG. 5 represents a potential coronary artery that may be compressed or pinched by tine portion 230 .
- the length of distal segment 232 is a factor contributing to the volume that is squeezed by penetrated tine portion 230 , so that reducing the length of distal segment 232 may be desired.
- an orientation of tine portion 230 relative to tissue T, when hook segment 231 is in the open position will be impacted such that tine portion 230 may be less likely to effectively penetrate into tissue T, for example, upon exiting through opening 313 of distal end 310 of catheter 300 ( FIGS. 3A-B ). Therefore, with reference to FIG.
- the tapering of hook segment 431 of tine portion 430 not only relieves strain but also allows for a more favorable orientation of the shorter distal segment 432 for tissue penetration (e.g., being directed along a line that is closer to normal to the tissue surface), when hook segment 431 is in the open position.
- tine portions for fixation of an implantable medical device incorporate a tapered hook segment and/or a shorter distal segment, to address the above described cyclic loading and/or potential tissue trauma.
- the following embodiments have been configured with reference to prior art tine portions of tissue-penetrating fixation components for medical devices, such as those described in the aforementioned commonly assigned U.S.
- patent application '690 (generally corresponding to tine portion 230 ), in order to allow a similar fit of devices, like device 200 , within a delivery catheter, for example, having the tine portions deformed into the open position within distal portion 310 of catheter 300 , and to maintain suitable baseline performance, for example, in terms of a deployment force (e.g., no greater than approximately 1-2 Newtons for a fixation component having four tine portions), an acute retraction force, for repositioning (e.g., between approximately 3-4 Newtons for a fixation component having four tine portions), atraumatic retraction, and an adequate acute fixation force (e.g., greater than approximately 2.5 Newtons for a fixation component having four tine portions).
- a deployment force e.g., no greater than approximately 1-2 Newtons for a fixation component having four tine portions
- an acute retraction force for repositioning
- atraumatic retraction e.g., greater than approximately 2.5 Newtons for a fixation component having four tine portions
- FIG. 6A is a plan view of a medical device 600 , according to some embodiments of the present invention.
- FIG. 6A illustrates device 600 including a hermitically sealed housing 620 and a pair of electrodes 661 , 662 ; housing 620 , like housing 220 of device 200 , contains control electronics and a power source (not shown), which, for example, together with electrodes 661 , 662 , are adapted for cardiac pacing and sensing.
- FIG. 6A further illustrates device 600 including tine portions 630 , which are adapted to penetrate tissue in order to secure device 600 at an implant site, for example, a cardiac site in the right atrium RA or the right ventricle RV ( FIG.
- tine portions 630 are included in a tissue-penetrating fixation component 63 , which is shown, separate from device 600 , in FIG. 6B .
- FIG. 6B illustrates component 63 also including a base portion 603 , from which tine portions 630 extend, preferably being integrally formed therewith, as described below.
- base portion 603 of fixation component 63 defines a longitudinal axis 6 of component 63 and is configured for attachment to device 600 so that axis 6 is approximately aligned with a longitudinal axis 20 of device 600 .
- Component 63 may be part of a subassembly that forms a distal end of device 600 , and which also includes electrode 661 ; such a subassembly is described in the aforementioned commonly-assigned U.S. patent application '690, in conjunction with FIGS. 3A-4B thereof, the description of which is hereby incorporated by reference.
- FIG. 6B further illustrates each tine portion 630 of tissue-penetrating component 63 including a hook segment 631 and a distal segment 632 .
- each hook segment 631 extends along a pre-set curvature that encloses an angle 8 , from a proximal end 61 thereof to a distal end 62 thereof.
- FIG. 6C illustrates each distal segment 632 extending along a relatively straight line that is approximately tangent to distal end 62 of hook segment 631 .
- angle 8 is less than 180 degrees, such that distal segment 632 extends away from axis 6 .
- FIG. 6C further illustrates the preset curvature of hook segment 631 being defined by a single radius R.
- radius R is approximately 0.085 inch
- an angle ⁇ , at which distal segment extends relative to axis 6 is approximately 20 degrees
- a length LD of distal segment 632 is between approximately 0.05 inch and approximately 0.1 inch.
- component 63 is manufactured by, first, laser cutting base portion 603 and tine portions 630 , together, from a tube of superelastic and biocompatible metal (e.g., Nitinol), and then wrapping and holding each tine portion 630 about a mandrel for a heat setting process that pre-sets the illustrated curvature of each hook segment 631 . Manufacturing methods such as these are known to those skilled in the art of forming Nitinol components.
- FIG. 6B shows base portion 603 of component 63 formed as a ring, wherein tine portions 630 are integrally formed therewith and spaced apart from one another about a perimeter of the ring, in alternate embodiments of tissue penetrating fixation components, one or more tine portions may be formed individually and then attached to a base portion that is configured in any suitable fashion for attachment to device 600 .
- FIG. 6D is a plan view of one of tine portions 630 , prior to forming the pre-set curvature thereof, in which the above-described tapering for strain relief along hook segment 631 , from first width W1 to smaller, second width W2 may be seen.
- component 63 is manufactured from Nitinol tubing that has a thickness of approximately 0.005 inch, and hook segment 631 thereof has a length LH of approximately 0.23 inch
- first width W1 may be between approximately two to five times greater than second width W2 to provide strain relief for improved fatigue life.
- first width W1 is between approximately 0.034 inch and approximately 0.05 inch
- second width W2 is approximately 0.010 inch
- third width W3 is approximately 0.02 inch.
- FIG. 7A is an elevation view of a tissue-penetrating fixation component 73 , according to some alternate embodiments of the present invention, which may be incorporated in device 600 as an alternative to component 63 , such that a longitudinal axis 7 of component 73 is approximately aligned with longitudinal axis 20 of device 600 .
- FIG. 7A illustrates component 73 including a base portion 703 , similar to base portion 603 of component 63 , and a plurality of tine portions 730 , each of which includes a hook segment 731 and a distal segment 732 . Tine portions 730 and base portion 703 are preferably integrally formed according to the method described above for component 63 .
- each tine portion 730 prior to the pre-setting of a curvature of hook segment 731 , may be configured like tine portion 630 as described above in conjunction with FIG. 6D , wherein the aforementioned exemplary values for widths W1, W2, W3, thickness t and lengths LD, LH are suitable.
- the pre-set curvature of hook segment 731 is defined by a single radius R, which may be approximately 0.085 inch.
- FIG. 7B is an estimated penetration path and an ‘as set’ relaxation plot for tine portion 730 of component 73 , which may be compared to that of tine portion 230 ( FIG. 5 ).
- FIG. 7B illustrates, with a solid line, tine portion 730 having been elastically deformed into the open position, for example, as would be the case when device 600 includes component 73 and is loaded within a delivery catheter, for example, distal end 310 of delivery catheter 300 ( FIG. 3A ).
- a delivery catheter for example, distal end 310 of delivery catheter 300 ( FIG. 3A ).
- the strain relief of tapering flattens the deformed profile of tine portion 730 relative to that of tine portion 230 , and that the open position of tine portion 730 orients distal segment 732 of tine portion 730 along a line that is nearly normal to the ordinate axis, which generally corresponds to the above-described tissue surface, for effective tissue penetration.
- tine portion 730 does not encompass as large a volume of tissue, relative to the pre-set curvature, toward which the penetrated tine portion 730 relaxes over time, upon full penetration, so that the above described risk of perforation and/or pinching of blood vessels is reduced.
- FIGS. 8A-B are plan views of tine portions 830 A, 830 B, prior to pre-setting a curvature thereof, according to some alternate embodiments, either of which may be formed in component 63 , 73 in lieu of tine portions 630 , 730 , for example, to increase the ease of tolerance control and inspection.
- FIGS. 8A-B illustrate hook segments 831 A, 831 B of tine portions 830 A, 830 B having a single-sided, or asymmetric taper. According to the illustrated embodiments, widths W1, W2, and W3 are designated at generally the same locations along hook segments 831 A, 831 B and distal segments 832 A, 832 B, as previously described for tine portions 630 and 730 .
- each tine portion 830 A, 830 B (into the page), for example, approximately 0.005 inch, is approximately constant along an entire length of each tine portion 830 A, 830 B, since components that would include tine portions 830 A, 830 B are preferably formed from a Nitinol tube according to the method described above.
- FIG. 8A further illustrates distal segment 832 A of tine portion 830 A being terminated in a tissue-piercing tip 822 , at which width W3 has a center line that is offset from a center line of second width W2; while FIG.
- first width W1 is between approximately 0.034 inch and approximately 0.05 inch
- second width W2 is approximately 0.010 inch
- third width W3 is approximately 0.02 inch.
- FIGS. 9A-D are profiles and corresponding estimated penetration path and ‘as set’ relaxation plots of various tine portions 930 A, 930 B, 930 C, 930 D, according to yet further embodiments of the present invention, wherein the profiles, per the pre-set curvatures of hook segments 931 A-D, accommodate for a relatively shorter length of distal segments 932 A-D thereof, for example, compared to that of tine portion 230 ( FIG. 5 ).
- FIGS. 9A-D illustrate the pre-set curvature of each hook segment 931 A-D being defined by two radii, R1 and R2, wherein R2 is greater than R1.
- radius R1 is approximately 1.04 mm and radius R2 is approximately 1.65 mm
- radius R1 is approximately 0.5 mm and radius R2 is approximately 1.65 mm
- radius R1 is 0.25 mm and radius R2 is approximately 2.4 mm.
- a tapering of hook segments 931 A-D will provide strain relief for improved fatigue life and allow for shorter tine portions 930 A-D without compromising the orientation of distal segments 932 A-D, when hook segments 931 A-D are deformed into the open position.
- Each of tine portions 930 A-D may be one of a plurality, which are included in a tissue-penetrating component, and that extend from a base portion 903 of the component, wherein base portion 903 defines an axis 9 of the component, and may be similar to the above described base portions 603 , 703 of components 63 , 73 .
- FIGS. 9A-D further illustrate each of tine portions 930 A-D including a proximal segment 933 A-D that extends between base portion 903 and the corresponding hook portion 931 A-D.
- proximal segments 933 A, 933 B is shown extending approximately parallel to axis 9
- each of proximal segments 933 C, 933 D is shown extending from base portion 903 toward axis 9 , for example, to increase an overall arc length of each of tine portions 930 C, 930 D for added flexibility during retraction into catheter distal end 310 ( FIGS. 3A-C ), when the corresponding hook segment 931 C, 931 D is being elastically deformed to the open position (solid line of plots).
- distal segments 932 C, 932 D when tine portions 930 C, 930 D are in the open position, is less favorable for ease of tissue penetration that that of other embodiments, the extension of proximal segments 933 C, 933 D toward axis 9 can contribute to a reduction in compressed tissue volume without a tapering of hook segments 931 C, 931 D.
- each hook portion 931 B, 931 C is also defined by a straight section S that extends between radii R1, R2.
- straight sections S can somewhat flatten the opened profile of tine portions 930 B, 930 C.
- FIGS. 10A-C and FIGS. 11A-B additional embodiments of the present invention, which are described below in conjunction with FIGS. 10A-C and FIGS. 11A-B , include tissue-piercing distal tips that are configured to enhance initial tine penetration.
- the initial penetration of tine portions 230 rely upon a stiffness of tine portions 230 being greater than that of tissue T, and upon an orientation of tissue-piercing tip 322 relative to tissue T, when device 200 is loaded in catheter distal end 310 , with hook segments 31 elastically deformed into the open position.
- FIG. 10A is a plan view of an implantable medical device 500 , according to some embodiments of the present invention.
- FIG. 10A illustrates device 500 including a hermitically sealed housing 520 and a pair of electrodes 561 , 562 ; housing 520 , like housing 220 of device 200 , contains control electronics and a power source (not shown), which, for example, together with electrodes 561 , 562 , are adapted for cardiac pacing and sensing.
- FIG. 10A further illustrates device 500 including tine portions 530 , which are adapted to penetrate tissue in order to secure device 500 at an implant site, for example, a cardiac site in the right atrium RA or the right ventricle RV ( FIG. 1 ).
- FIG. 10B is a perspective view of a tissue-penetrating fixation component 53 , according to some embodiments of the present invention, which is shown separated from device 500 , and which includes tine portions 530 .
- FIG. 10B illustrates component 53 also including a base portion 503 , from which tine portions 530 extend.
- base portion 503 of fixation component 53 defines a longitudinal axis 5 of component 53 and is configured for attachment to device 500 so that axis 5 is approximately aligned with a longitudinal axis 25 of device 500 .
- Component 53 may be part of a subassembly that forms a distal end of device 500 , and which also includes electrode 561 , for example, like the aforementioned subassembly that is disclosed in the above referenced and incorporated by reference passages of the detailed description of commonly-assigned U.S. patent application '690.
- FIG. 10B further illustrates each tine portion 530 of tissue-penetrating fixation component 53 including a hook segment 531 and a distal segment 532 .
- Each hook segment 531 is shown extending along a curvature that encloses an angle ⁇ , from a proximal end 51 thereof to a distal end 52 thereof; and each distal segment 532 is shown extending along a relatively straight line that is approximately tangent to distal end 52 of hook segment 531 .
- Each distal segment 532 is shown extending toward axis 5 , and, according to an exemplary embodiment, angle ⁇ is approximately 200 degrees.
- component 53 is manufactured by, first, laser cutting base portion 503 and tine portions 530 , together, from a tube of superelastic and biocompatible metal (e.g., Nitinol), and then wrapping and holding each tine portion 530 about a mandrel for a heat setting process that pre-sets the illustrated curvature of each hook segment 531 .
- a tube of superelastic and biocompatible metal e.g., Nitinol
- 10B shows base portion 503 of component 53 formed as a ring, wherein tine portions 530 are integrally formed therewith, and spaced apart from one another about a perimeter of the ring, in alternate embodiments of tissue penetrating fixation components, one or more tine portions may be formed individually and then attached to a base portion that is configured in any suitable fashion for attachment to device 500 .
- a length of distal segment 632 of each tine portion 630 is relatively short compared to that of distal segment 232 of tine portion 230 , for example, between approximately 0.05 inch and approximately 0.1 inch.
- the shorter length can help to prevent perforation through the wall of a structure, for example, the heart, at some implant locations, and can reduce a probability for penetrated tine portions 530 to interfere with blood vessels, which interference, for example, may compromise coronary blood supply, as described above.
- each distal segment 532 includes a tooth 520 and a relatively blunt end 540 , which surrounds tooth 520 .
- FIG. 10B illustrates end 540 including a pair of legs 541 and a distal arch 542 that extends between legs 541 , distal to tip 522 of tooth 520 , for example, being spaced apart therefrom by approximately 0.005 inch.
- Each tooth 520 has a length, which is defined from a foot 521 thereof to a tissue-piercing tip 522 thereof, for example, being between approximately 0.025 inch and approximately 0.045 inch, and legs 541 extend along the length of tooth 520 , on opposing sides thereof.
- Each tooth 520 and corresponding end 540 may be laser cut at the same time that tine portions 530 and base portion 503 are cut from the aforementioned tube.
- legs 541 of end 540 are configured to bend in elastic deformation when distal arch 542 is pushed against tissue at a potential implant site, for example, as illustrated in FIG. 10C , so that tip 522 of tooth 520 , which is configured to resist bending, is exposed to pierce the tissue.
- FIG. 10C is an enlarged detail view of distal segment 532 as tine portion 530 is pushed into contact with tissue T at the implant site.
- pushing distal arch 542 against the tissue T may be accomplished, as described above for device 200 , after device 500 is loaded into distal end 310 of catheter 300 so that hook segments 531 of tine portions 530 are elastically deformed into the open position, at which distal segments 532 are directed distally toward opening 313 of distal end 310 .
- legs 541 of end 540 can relax back into line with tooth 520 so that distal arch 542 , upon subsequent penetration/insertion of tine portions 530 into tissue, and upon retraction thereof from the tissue, if necessary, prevents tip 522 from tearing the tissue.
- a thickness t of each tine portion 530 which is relatively constant along the entire length thereof, is approximately 0.005 inch
- a width wf of foot 521 of tooth 520 is between approximately 0.010 inch and approximately 0.015 inch
- a width wt of tip 522 of tooth 520 is approximately 0.003 inch
- a width we of legs 541 and distal arch 542 is approximately 0.005 inch.
- FIG. 11A is an elevation view of a tissue-penetrating fixation component 83 , according to some alternate embodiments of the present invention, which may also be incorporated in the exemplary device of FIG. 10A .
- FIG. 11A illustrates component 83 including a base portion 803 and a plurality of tine portions 830 extending therefrom, similar to component 53 , wherein each tine portion 830 includes a hook segment 831 and a distal segment 832 that are configured to address both of the aforementioned issues related to tissue penetration and fatigue life.
- Component 83 may be cut and formed from a Nitinol tube in a manner similar to that described above for component 53 .
- each hook segment 831 being pre-set to extend along a curvature that encloses angle ⁇ , from a proximal end 81 thereof to a distal end 82 thereof; and each distal segment 832 is shown extending along a relatively straight line that is approximately tangent to distal end 82 of hook segment 831 .
- angle ⁇ is approximately 180 degrees, so that each distal segment 832 extends approximately parallel to a longitudinal axis 8 of component 83 .
- the pre-set curvature of hook segment 831 is defined by a single radius R, which may be approximately 0.085 inch.
- FIG. 11B is a plan view of tine portion 830 , prior to forming the pre-set curvature thereof.
- FIGS. 11A-B illustrate each tine portion 830 including a tapered hook portion 831 , similar to hook portions 631 , 731 of tine portions 630 , 730 , described above, wherein second width W2, in proximity to distal end 82 of hook segment 831 , is less than first width W1, in proximity to a proximal end 81 of hook segment 831 .
- FIGS. 11A-B further illustrate distal segment 832 having a width W3 that is greater than the second width W2.
- Distal segment 832 like distal segment 532 of component 53 , includes tooth 520 and end 540 to facilitate tissue piercing without tearing, as described above.
- a thickness t of each tine portion 830 which is relatively constant along the entire length thereof, may be approximately 0.005 inch, and distal segment 832 thereof may conform to the aforementioned exemplary dimensions of tooth 520 and end 540 .
Landscapes
- Health & Medical Sciences (AREA)
- Cardiology (AREA)
- Heart & Thoracic Surgery (AREA)
- Life Sciences & Earth Sciences (AREA)
- Engineering & Computer Science (AREA)
- Biomedical Technology (AREA)
- Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
- Radiology & Medical Imaging (AREA)
- Animal Behavior & Ethology (AREA)
- General Health & Medical Sciences (AREA)
- Public Health (AREA)
- Veterinary Medicine (AREA)
- Vascular Medicine (AREA)
- Media Introduction/Drainage Providing Device (AREA)
- Prostheses (AREA)
- Surgical Instruments (AREA)
Abstract
Description
- The present application is related to the commonly-assigned United States patent application having the Attorney Docket number C00002846.USU1 and C00003103.USU1, which are filed concurrently herewith and incorporated by reference, in their entirety.
- The present invention pertains to implantable medical devices, and, more specifically, to tissue-penetrating fixation components thereof.
- An implantable medical device, for the delivery of stimulation therapy and/or for diagnostic sensing, may include at least one tissue-penetrating fixation component configured to hold the device at an implant location.
FIG. 1 is a schematic diagram that shows potential cardiac implant sites for such a device, for example, within anappendage 102 of a right atrium RA, within a coronary vein CV (via a coronary sinus ostium CSOS), or in proximity to anapex 103 of a right ventricle RV.FIG. 2 is a plan view of an exemplary implantablemedical device 200, which includes a tissue-penetrating fixation component formed by a plurality oftine portions 230.FIG. 2 further illustratesdevice 200 including a hermitically sealedhousing 220 that contains control electronics and a power source (not shown), and which defines alongitudinal axis 2 ofdevice 200.Housing 220 may be formed from a medical grade stainless steel or titanium alloy and have an insulative layer formed thereover, for example, parylene, polyimide, or urethane. With further reference toFIG. 2 ,device 200 includes a pair ofelectrodes portions 230surround electrode 261 and are configured to penetrate tissue in order to holdelectrode 261 in intimate contact with tissue, for example, at one of the aforementioned implant sites, while securing, or fixatingdevice 200 for chronic implantation at the site. Further description of a suitable construction fordevice 200 may be found in the co-pending and commonly assigned United States patent application having the pre-grant publication number 2012/0172690 A1. - With reference to
FIG. 3A ,device 200 may be delivered to an implant location via adelivery catheter 300. For example, with reference toFIG. 1 , if the target implant site is located in the right atrium RA, coronary vein CV, or right ventricle RV, adistal end 310 ofcatheter 300 may be maneuvered into the heart through a superior vena cava SVC or an inferior vena cava IVC, according to a transvenous delivery method known in the art.FIG. 3A shows a partial cross-section ofdistal end 310 ofcatheter 300, which is formed like a cup to hold and containdevice 200 for delivery to the implant site.FIG. 3A illustratesdevice 200 having been loaded intodistal end 310 so that ahook segment 231 of eachtine portion 230 is elastically deformed, from a pre-set curvature thereof, to an open position, at which adistal segment 232 of eachtine portion 230 extends distally toward an opening 313 of catheterdistal end 310. Eachtine portion 230 is preferably formed from a superelastic material, such as Nitinol.FIG. 3A further illustrates adeployment element 320 abutting a proximal end ofdevice 200 and extending proximally therefrom, through a lumen ofcatheter 300, and out from aproximal opening 301 thereof. Element 320 may be moved, per arrow M, by an operator to pushdevice 200, per arrow P, out from opening 313 ofdistal end 310, for example, when opening 313 has been located by the operator in close proximity to tissue at the target implant site. -
FIG. 3B , is an enlarged view ofdistal segment 232 of one oftine portions 230, wherein a tissue-piercing tip 322, which terminatesdistal segment 232, has just been pushed out through opening 313 ofdistal end 310 ofcatheter 300 and into contact with tissue T.FIG. 3B illustratesdistal segment 232 supported by the surrounding wall ofdistal end 310, in proximity to opening 313, so that the push force ofdeployment element 320 is effectively transferred throughtip 322 to first compress the tissue T, as shown, and then to pierce the tissue T for penetration therein, which is shown inFIGS. 3C-D .FIGS. 3C-D illustrate partial tine penetration and full tine penetration, respectively, asdeployment element 320 continues to pushdevice 200 out opening 313. It can be seen that the elastic nature of eachtine portion 230, once the constraint of thedistal end 310 is withdrawn, allows thecorresponding hook segment 231 to relax back toward the pre-set curvature thereof within the tissue. The full penetration oftine portions 230, shownFIG. 3D , is representative of acute fixation ofdevice 200 at the implant site, for example, for the evaluation of device performance (e.g., pacing and sensing viaelectrodes 261, 262). It should be noted that, at some implant sites, tineportions 230 may, at full penetration, extend back out from tissue T, for example, generally towarddistal end 310 ofcatheter 300. - With further reference to
FIG. 3D , atether 350 is shown looping through aneye feature 205 formed at the proximal end ofdevice 200;tether 350 extends proximally through a lumen ofdeployment element 320 to aproximal end 351 thereof, outside a proximal end ofdeployment element 320, which may be seen inFIG. 3A . Thus, if the performance of acutely fixateddevice 200 is unsatisfactory, the operator may usetether 350 to pulldevice 200 back intodistal end 310, thereby withdrawingtine portions 230 from the tissue, so that device may be moved bydelivery catheter 300 to another potential implant site. Alternately, if the acutely fixateddevice 200 performs satisfactorily,proximal end 351 oftether 350 may be severed to pulltether 350 out fromeye feature 205 ofdevice 200, and the fully penetratedtine portions 230 continue to fixatedevice 200 for chronic implant. - The aforementioned co-pending and commonly assigned U.S. patent application '690 discloses suitable embodiments of a fixation component having tine portions similar to
tine portions 230, wherein the tine portions exhibit a suitable baseline performance, for example, in terms of a deployment force, an acute retraction force (for repositioning), atraumatic retraction, and acute and chronic fixation forces. Yet, there is still a need for new configurations of tine portions for implantable devices, likedevice 200, that may further enhance fixation. - Embodiments of the present invention encompass implantable medical devices (e.g., cardiac pacemakers) and tissue-penetrating fixation components thereof, which include one or more tine portions that are configured to mitigate the risk of compressing, for example, to the point of occlusion, blood vessels in proximity to the implant site, and to reduce the risk of tissue trauma during the retraction thereof from the tissue, for example, for repositioning. In certain embodiments, the tine portions may also be configured for increased strain relief during the flexing thereof, either at initial implant (particularly in cases where the retraction of penetrated tines is necessary for repositioning the device), or when subject to cyclic loading during a chronic implant of the fixated device, for example, within a beating heart.
- According to some embodiments, a tine portion of a tissue-penetrating component of an implantable medical device includes a hook segment and a relatively short distal segment, wherein the distal segment includes a tooth and an end that surrounds the tooth. The hook segment is elastically deformable from a pre-set curvature thereof to an open position, and the distal segment is pre-set to extend from a distal end of the hook segment along a relatively straight line that is approximately tangent to the distal end. The end of the distal segment includes a pair of legs and a distal arch, wherein the legs extend along a length of the tooth, on opposing sides thereof, and the distal arch extends between the legs and distal to a tissue-piercing tip of the tooth. The legs of the end are configured to bend in elastic deformation, when the hook segment is elastically deformed to the open position and a force is applied to push the distal arch of the distal segment against tissue, for initial tissue penetration, so that the bending of the legs expose the tip of the tooth to the tissue.
- The tissue-penetrating component, according to some embodiments, further includes a base portion, for example, in the form of a ring, that is configured to be fixedly attached to the implantable medical device, wherein the tine portion may be one of a plurality of tine portions integrally formed with the base portion. According to some preferred embodiments, each tine portion has a substantially constant thickness along an entire length thereof, from a proximal end of the hook segment to the distal arch of the end of the distal segment. Strain relief of each tine portion may be provided by a tapering of the hook segment thereof, from a first width thereof, in proximity to the proximal end thereof, to a second, smaller width thereof, in proximity to a distal end thereof. And, in some of the tapering embodiments, a width of distal segment, defined by the pair of legs thereof, is greater than the second width of the hook segment.
- The following drawings are illustrative of particular embodiments of the present invention and therefore do not limit the scope of the invention. The drawings are not to scale (unless so stated) and are intended for use in conjunction with the explanations in the following detailed description. Embodiments will hereinafter be described in conjunction with the appended drawings wherein like numerals/letters denote like elements, and:
-
FIG. 1 is a schematic diagram showing potential implant sites for embodiments of the present invention; -
FIG. 2 is a plan view of an exemplary implantable medical device; -
FIG. 3A is a plan view of the medical device loaded in a delivery catheter, according to some embodiments, wherein tine portions of a tissue-penetrating fixation component thereof are elastically deformed into an open position; -
FIG. 3B is an enlarged detail view of one of the tine portions initially contacting tissue at an implant site; -
FIGS. 3C-D are plan views of the device and catheter in subsequent steps of implanting the device, when the tine portions have penetrated the tissue; -
FIG. 4A is a schematic representation of a flexing tine portion; -
FIG. 4B is a perspective view of a tapered tine portion, according to some embodiments of the present invention; -
FIG. 5 is an estimated penetration path and an ‘as set’ relaxation plot for a tine portion of the exemplary device shown inFIG. 2 ; -
FIG. 6A is a plan view of an implantable medical device, according to some embodiments of the present invention; -
FIG. 6B is a perspective view of a tissue-penetrating fixation component, according to some embodiments of the present invention, separated from the device ofFIG. 6A ; -
FIG. 6C is an elevation view of the component ofFIG. 7B , according to some embodiments; -
FIG. 6D is a plan view of a tine portion of the component ofFIG. 7B , according to some embodiments; -
FIG. 7A is an elevation view of a tissue-penetrating fixation component, according to some alternate embodiments, which may be incorporated in the device ofFIG. 6A ; -
FIG. 7B is an estimated penetration path and an ‘as set’ relaxation plot for a tine portion of the component shown inFIG. 7A ; -
FIGS. 8A-B are plan views of tine portions, according to some alternate embodiments; -
FIGS. 9A-D are profiles and corresponding estimated penetration path and ‘as set’ relaxation plots of various tine portions, according to additional embodiments; -
FIG. 10A is a plan view of an implantable medical device, according to some alternate embodiments of the present invention; -
FIG. 10B is a perspective view of a tissue-penetrating fixation component, according to some embodiments, separated from the device ofFIG. 10A ; -
FIG. 10C is an enlarged detail view of a distal segment of one of the tine portions of theFIG. 10B component initially contacting tissue at an implant site; -
FIG. 11A is an elevation view of a tissue-penetrating fixation component, according to yet further embodiments of the present invention, which may be incorporated in the exemplary device ofFIG. 10A ; and -
FIG. 11B is a plan view of a tine portion of the component ofFIG. 11A , according to some embodiments. - The following detailed description is exemplary in nature and is not intended to limit the scope, applicability, or configuration of the invention in any way. Rather, the following description provides practical examples, and those skilled in the art will recognize that some of the examples may have suitable alternatives.
-
FIG. 4A is a schematic representation of one oftine portions 230 isolated from the above-described implantablemedical device 200, wherein an exemplary flexing, per arrow F, oftine portion 230 is illustrated. Such flexing may be encountered bytine portion 230, oncetine portion 230 has penetrated tissue to fixdevice 200 at a chronic implant site for cardiac monitoring and/or therapy, for example, as illustrated inFIG. 3D . Thus, fatigue life is a consideration influencing the configuration of tine portions for those implantable medical devices that may be subjected to cyclic loading caused by hundreds of millions of heart beats, over the life of their implant. InFIG. 4A , a zone of stress concentration SC, for example, in response to the flexing per arrow F, is circled; zone SC is located in proximity to aproximal end 31 ofhook segment 231 oftine portion 230, wherehook segment 231 joins with abase portion 203.Base portion 203 andtine portion 230 may be integrally formed, whereinbase portion 203 is configured to be fixedly attached todevice 200. Stress concentration in zone SC may also result from deformation ofhook segment 231 into the open position (FIG. 3A ), for example, upon initial loading ofdevice 200 and retraction ofdevice 200 back intodistal end 310 of catheter for repositioning, which, in combination with the repeated force of deployment, can potentially pushtine portion 230 toward an elastic limit and may maketine portion 230 subsequently more vulnerable to fatigue under the aforementioned cyclic loading. Although rounded edges oftine portions 230 effectively reduce the concentration of stress, as previously described in the aforementioned commonly-assigned U.S. patent application '690, some embodiments of the present invention incorporate tine portions that have tapered hook segments to further address the stress concentration, for example, as illustrated inFIG. 4B . -
FIG. 4B is a perspective view of atine portion 430, according to some embodiments, one or more of which may be integrated intodevice 200, as substitute fortine portions 230. Abase portion 403 is shown integrally formed withtine portion 430, according to some preferred embodiments, whereinbase portion 403 is configured for attachment to a medical device, such asdevice 200.FIG. 4B illustrates ahook segment 431 oftine portion 430 extending from afirst end 41 thereof, in proximity tobase portion 403, to asecond end 42 thereof, in proximity to adistal segment 432 oftine portion 430, whereinhook segment 431 tapers from a first width W1, in proximity toproximal end 41, to a smaller, second width W2, in proximity to adistal end 42 ofhook segment 431. The tapering ofhook segment 431 provides strain relief during the aforementioned deformation/flexing, to alleviate the aforementioned stress concentration.FIG. 4B further illustrates an optional slot 48 (dashed lines), which may be formed through a thickness t oftine portion 430, and extend between first width W1 and second width W2. The inclusion ofslot 48 provides an additional means for providing strain relief, for example, when a limit on how narrow second width W2 may be, for example, no smaller than approximately 0.020-0.025 inch, so thatdistal segment 432 does not tear tissue upon retraction therefrom. According to some embodiments,optional slot 48 may include internal shear tabs (not shown) to help distribute out of plane loads, for example, orthogonal to the illustrated direction of flexing, per arrow F ofFIG. 4A . - With further reference to
FIGS. 4A-B ,distal segment 432 oftine portion 430 is shown having a shorter length thandistal segment 232 oftine portion 230, for example, to provide more flexibility in selecting a suitable implant site without risking undue trauma to tissue, upon penetration oftine portion 430 at the selected site. The shorter length can help to prevent perforation through the wall of a structure, for example, the heart, at some implant locations, and can reduce a probability for penetratedtine portions 430 to interfere with blood vessels, which interference, for example, may compromise coronary blood supply, as will be described below in conjunction withFIG. 5 . -
FIG. 5 is an estimated tissue penetration path and an ‘as set’ relaxation plot fortine portion 230 of device 200 (FIG. 2 ), whereintine portion 230 is formed from approximately 0.005 inch thick Nitinol.FIG. 5 includes a solid line, which represents the profile oftine portion 230 whendevice 200 is loaded indistal end 310 of catheter 300 (FIG. 3A ) withhook segment 231 deformed to the open position. With reference back toFIGS. 3A-D , the origin, or zero coordinate, along the ordinate axis generally corresponds to the constraining wall ofdistal segment 310 ofdelivery catheter 300. The plot ofFIG. 5 is made up of a segmented line connecting circles, which corresponds to the estimated penetration path oftine portion 230, for example, whendevice 200 is pushed out fromdistal end 310 and into tissue T (FIGS. 3B-D ), and a dashed line, which represents the profile oftine portion 230, according to the pre-set curvature, toward which the penetratedtine portion 230 relaxes over time. The volume of tissue between the segmented line and the dashed line approaches that which is squeezed or compressed by the penetratedtine portion 230 as it relaxes over time; the greater this volume, the greater the probability for the penetrated tine to compress or pinch one or more blood vessels that perfuse the tissue. For example, the dotted line inFIG. 5 represents a potential coronary artery that may be compressed or pinched bytine portion 230. As alluded to above, the length ofdistal segment 232 is a factor contributing to the volume that is squeezed by penetratedtine portion 230, so that reducing the length ofdistal segment 232 may be desired. However, if the length ofdistal segment 232 is reduced, without modifying other aspects oftine portion 230, an orientation oftine portion 230 relative to tissue T, whenhook segment 231 is in the open position, will be impacted such thattine portion 230 may be less likely to effectively penetrate into tissue T, for example, upon exiting throughopening 313 ofdistal end 310 of catheter 300 (FIGS. 3A-B ). Therefore, with reference toFIG. 4B , the tapering ofhook segment 431 oftine portion 430 not only relieves strain but also allows for a more favorable orientation of the shorterdistal segment 432 for tissue penetration (e.g., being directed along a line that is closer to normal to the tissue surface), whenhook segment 431 is in the open position. - Various embodiments of tine portions for fixation of an implantable medical device, for example, as described below, incorporate a tapered hook segment and/or a shorter distal segment, to address the above described cyclic loading and/or potential tissue trauma. The following embodiments have been configured with reference to prior art tine portions of tissue-penetrating fixation components for medical devices, such as those described in the aforementioned commonly assigned U.S. patent application '690 (generally corresponding to tine portion 230), in order to allow a similar fit of devices, like
device 200, within a delivery catheter, for example, having the tine portions deformed into the open position withindistal portion 310 ofcatheter 300, and to maintain suitable baseline performance, for example, in terms of a deployment force (e.g., no greater than approximately 1-2 Newtons for a fixation component having four tine portions), an acute retraction force, for repositioning (e.g., between approximately 3-4 Newtons for a fixation component having four tine portions), atraumatic retraction, and an adequate acute fixation force (e.g., greater than approximately 2.5 Newtons for a fixation component having four tine portions). -
FIG. 6A is a plan view of amedical device 600, according to some embodiments of the present invention.FIG. 6A illustratesdevice 600 including a hermitically sealedhousing 620 and a pair ofelectrodes housing 620, likehousing 220 ofdevice 200, contains control electronics and a power source (not shown), which, for example, together withelectrodes FIG. 6A further illustratesdevice 600 includingtine portions 630, which are adapted to penetrate tissue in order to securedevice 600 at an implant site, for example, a cardiac site in the right atrium RA or the right ventricle RV (FIG. 1 ), having been deployed fromdistal end 310 of delivery catheter 300 (FIGS. 3A-D ). According to some embodiments,tine portions 630 are included in a tissue-penetratingfixation component 63, which is shown, separate fromdevice 600, inFIG. 6B . -
FIG. 6B illustratescomponent 63 also including abase portion 603, from which tineportions 630 extend, preferably being integrally formed therewith, as described below. According to the illustrated embodiment,base portion 603 offixation component 63 defines alongitudinal axis 6 ofcomponent 63 and is configured for attachment todevice 600 so thataxis 6 is approximately aligned with alongitudinal axis 20 ofdevice 600.Component 63 may be part of a subassembly that forms a distal end ofdevice 600, and which also includeselectrode 661; such a subassembly is described in the aforementioned commonly-assigned U.S. patent application '690, in conjunction withFIGS. 3A-4B thereof, the description of which is hereby incorporated by reference.FIG. 6B further illustrates eachtine portion 630 of tissue-penetratingcomponent 63 including ahook segment 631 and adistal segment 632. - With reference to
FIG. 6C , which is an elevation view ofcomponent 63, eachhook segment 631 extends along a pre-set curvature that encloses anangle 8, from aproximal end 61 thereof to adistal end 62 thereof.FIG. 6C illustrates eachdistal segment 632 extending along a relatively straight line that is approximately tangent todistal end 62 ofhook segment 631. According to the illustrated embodiment,angle 8 is less than 180 degrees, such thatdistal segment 632 extends away fromaxis 6.FIG. 6C further illustrates the preset curvature ofhook segment 631 being defined by a single radius R. According to an exemplary embodiment, radius R is approximately 0.085 inch, an angle β, at which distal segment extends relative toaxis 6, is approximately 20 degrees, and a length LD ofdistal segment 632 is between approximately 0.05 inch and approximately 0.1 inch. - According to some preferred embodiments,
component 63 is manufactured by, first, lasercutting base portion 603 andtine portions 630, together, from a tube of superelastic and biocompatible metal (e.g., Nitinol), and then wrapping and holding eachtine portion 630 about a mandrel for a heat setting process that pre-sets the illustrated curvature of eachhook segment 631. Manufacturing methods such as these are known to those skilled in the art of forming Nitinol components. AlthoughFIG. 6B showsbase portion 603 ofcomponent 63 formed as a ring, whereintine portions 630 are integrally formed therewith and spaced apart from one another about a perimeter of the ring, in alternate embodiments of tissue penetrating fixation components, one or more tine portions may be formed individually and then attached to a base portion that is configured in any suitable fashion for attachment todevice 600. -
FIG. 6D is a plan view of one oftine portions 630, prior to forming the pre-set curvature thereof, in which the above-described tapering for strain relief alonghook segment 631, from first width W1 to smaller, second width W2 may be seen. When, for example, in the aforementioned exemplary embodiment,component 63 is manufactured from Nitinol tubing that has a thickness of approximately 0.005 inch, andhook segment 631 thereof has a length LH of approximately 0.23 inch, first width W1 may be between approximately two to five times greater than second width W2 to provide strain relief for improved fatigue life. Yet, if the smaller, second width W2, for example, being approximately 0.010 inch, were to define an entirety ofdistal segment 632,distal segment 632 may tear tissue upon retraction therefrom, for example, when repositioningdevice 600. So, with further reference toFIG. 6D ,distal segment 632 oftine portion 630 is terminated by a tissue-piercingtip 622 that has a width W3, which is greater than second width W2, for example, approximately two to three times greater, in order to be atraumatic to tissue. In the aforementioned exemplary embodiment, first width W1 is between approximately 0.034 inch and approximately 0.05 inch, second width W2 is approximately 0.010 inch, and third width W3 is approximately 0.02 inch. -
FIG. 7A is an elevation view of a tissue-penetratingfixation component 73, according to some alternate embodiments of the present invention, which may be incorporated indevice 600 as an alternative tocomponent 63, such that alongitudinal axis 7 ofcomponent 73 is approximately aligned withlongitudinal axis 20 ofdevice 600.FIG. 7A illustratescomponent 73 including abase portion 703, similar tobase portion 603 ofcomponent 63, and a plurality oftine portions 730, each of which includes ahook segment 731 and adistal segment 732.Tine portions 730 andbase portion 703 are preferably integrally formed according to the method described above forcomponent 63. Furthermore, eachtine portion 730, prior to the pre-setting of a curvature ofhook segment 731, may be configured liketine portion 630 as described above in conjunction withFIG. 6D , wherein the aforementioned exemplary values for widths W1, W2, W3, thickness t and lengths LD, LH are suitable. However, with further reference toFIG. 7A , the pre-set curvature along whichhook segment 731 extends, from afirst end 71 thereof and asecond end 72 thereof, encloses an angle φ, which is 180 degrees, so thatdistal segment 732 extends, between a tissue-piercingtip 722 thereof andsecond end 72 ofhook segment 731, along a line that is approximately parallel toaxis 7. The pre-set curvature ofhook segment 731, likehook segment 631, is defined by a single radius R, which may be approximately 0.085 inch. -
FIG. 7B is an estimated penetration path and an ‘as set’ relaxation plot fortine portion 730 ofcomponent 73, which may be compared to that of tine portion 230 (FIG. 5 ).FIG. 7B illustrates, with a solid line,tine portion 730 having been elastically deformed into the open position, for example, as would be the case whendevice 600 includescomponent 73 and is loaded within a delivery catheter, for example,distal end 310 of delivery catheter 300 (FIG. 3A ). In comparing the solid lines ofFIGS. 5 and 7B , it may be appreciated how the strain relief of tapering flattens the deformed profile oftine portion 730 relative to that oftine portion 230, and that the open position oftine portion 730 orientsdistal segment 732 oftine portion 730 along a line that is nearly normal to the ordinate axis, which generally corresponds to the above-described tissue surface, for effective tissue penetration. Furthermore, in comparing the estimated tissue penetration path oftine portions 230 and 730 (segmented lines connecting the circles), relative to the corresponding relaxed profiles (dashed lines), it can be seen that, due to the shorter length and more open pre-set curvature,tine portion 730 does not encompass as large a volume of tissue, relative to the pre-set curvature, toward which the penetratedtine portion 730 relaxes over time, upon full penetration, so that the above described risk of perforation and/or pinching of blood vessels is reduced. -
FIGS. 8A-B are plan views oftine portions component tine portions FIGS. 8A-B illustratehook segments tine portions hook segments distal segments tine portions tine portion tine portion tine portions FIG. 8A further illustratesdistal segment 832A oftine portion 830A being terminated in a tissue-piercing tip 822, at which width W3 has a center line that is offset from a center line of second width W2; whileFIG. 8B illustrates a tissue-piercingtip 822B ofdistal segment 832B, at which width W3 has a center line approximately aligned with that of second width W2. According to some exemplary embodiments, first width W1 is between approximately 0.034 inch and approximately 0.05 inch, second width W2 is approximately 0.010 inch, and third width W3 is approximately 0.02 inch. -
FIGS. 9A-D are profiles and corresponding estimated penetration path and ‘as set’ relaxation plots ofvarious tine portions hook segments 931A-D, accommodate for a relatively shorter length ofdistal segments 932A-D thereof, for example, compared to that of tine portion 230 (FIG. 5 ).FIGS. 9A-D illustrate the pre-set curvature of eachhook segment 931A-D being defined by two radii, R1 and R2, wherein R2 is greater than R1. According to exemplary embodiments oftine portions tine portion 930C, radius R1 is approximately 0.5 mm and radius R2 is approximately 1.65 mm, and, in an exemplary embodiment oftine portion 930D, radius R1 is 0.25 mm and radius R2 is approximately 2.4 mm. It should be noted that none oftine portions 930A-D, as depicted in the corresponding plots, include tapering along thecorresponding hook segments 931A-D thereof. Yet, it is contemplated that a tapering ofhook segments 931A-D, for example, similar to that described above, will provide strain relief for improved fatigue life and allow forshorter tine portions 930A-D without compromising the orientation ofdistal segments 932A-D, whenhook segments 931A-D are deformed into the open position. - Each of
tine portions 930A-D may be one of a plurality, which are included in a tissue-penetrating component, and that extend from abase portion 903 of the component, whereinbase portion 903 defines anaxis 9 of the component, and may be similar to the above describedbase portions components FIGS. 9A-D further illustrate each oftine portions 930A-D including aproximal segment 933A-D that extends betweenbase portion 903 and thecorresponding hook portion 931A-D. Each ofproximal segments axis 9, while each ofproximal segments base portion 903 towardaxis 9, for example, to increase an overall arc length of each oftine portions FIGS. 3A-C ), when thecorresponding hook segment 931C, 931D is being elastically deformed to the open position (solid line of plots). Furthermore, although the orientation ofdistal segments tine portions proximal segments axis 9 can contribute to a reduction in compressed tissue volume without a tapering ofhook segments 931C, 931D. - With further reference to
FIGS. 9B-C , eachhook portion FIGS. 9A-D , it may be seen how straight sections S can somewhat flatten the opened profile oftine portions FIG. 9A-D plots, which correspond to the estimated tissue penetration path of each oftine portions 930A-D, to that in theFIG. 5 plot fortine portion 230, it can be appreciated that the relatively shorter lengths ofdistal segments 932A-D, in combination with the corresponding profiles oftine portions 930A-D, lead to a reduction in tissue volume that is potentially compressed by each of the penetratedtine portions 930A-D during subsequent relaxation toward the pre-set curvature (dashed lines). - Because a reduction in the length, and/or tapering for strain relief of tine portions, can, in some instances, hinder initial tine penetration upon deployment (e.g., according to the method described above in conjunction with
FIGS. 3B-C ), additional embodiments of the present invention, which are described below in conjunction withFIGS. 10A-C andFIGS. 11A-B , include tissue-piercing distal tips that are configured to enhance initial tine penetration. With reference toFIGS. 3A-B , the initial penetration oftine portions 230 rely upon a stiffness oftine portions 230 being greater than that of tissue T, and upon an orientation of tissue-piercingtip 322 relative to tissue T, whendevice 200 is loaded in catheterdistal end 310, withhook segments 31 elastically deformed into the open position. -
FIG. 10A is a plan view of an implantablemedical device 500, according to some embodiments of the present invention.FIG. 10A illustratesdevice 500 including a hermitically sealedhousing 520 and a pair ofelectrodes housing 520, likehousing 220 ofdevice 200, contains control electronics and a power source (not shown), which, for example, together withelectrodes FIG. 10A further illustratesdevice 500 includingtine portions 530, which are adapted to penetrate tissue in order to securedevice 500 at an implant site, for example, a cardiac site in the right atrium RA or the right ventricle RV (FIG. 1 ). -
FIG. 10B is a perspective view of a tissue-penetratingfixation component 53, according to some embodiments of the present invention, which is shown separated fromdevice 500, and which includestine portions 530.FIG. 10B illustratescomponent 53 also including a base portion 503, from which tineportions 530 extend. According to the illustrated embodiment, base portion 503 offixation component 53 defines alongitudinal axis 5 ofcomponent 53 and is configured for attachment todevice 500 so thataxis 5 is approximately aligned with alongitudinal axis 25 ofdevice 500.Component 53 may be part of a subassembly that forms a distal end ofdevice 500, and which also includeselectrode 561, for example, like the aforementioned subassembly that is disclosed in the above referenced and incorporated by reference passages of the detailed description of commonly-assigned U.S. patent application '690. -
FIG. 10B further illustrates eachtine portion 530 of tissue-penetratingfixation component 53 including ahook segment 531 and adistal segment 532. Eachhook segment 531 is shown extending along a curvature that encloses an angle ψ, from aproximal end 51 thereof to adistal end 52 thereof; and eachdistal segment 532 is shown extending along a relatively straight line that is approximately tangent todistal end 52 ofhook segment 531. Eachdistal segment 532 is shown extending towardaxis 5, and, according to an exemplary embodiment, angle ψ is approximately 200 degrees. According to some preferred embodiments,component 53 is manufactured by, first, laser cutting base portion 503 andtine portions 530, together, from a tube of superelastic and biocompatible metal (e.g., Nitinol), and then wrapping and holding eachtine portion 530 about a mandrel for a heat setting process that pre-sets the illustrated curvature of eachhook segment 531. As mentioned above, manufacturing methods such as these are known to those skilled in the art of forming Nitinol components. AlthoughFIG. 10B shows base portion 503 ofcomponent 53 formed as a ring, whereintine portions 530 are integrally formed therewith, and spaced apart from one another about a perimeter of the ring, in alternate embodiments of tissue penetrating fixation components, one or more tine portions may be formed individually and then attached to a base portion that is configured in any suitable fashion for attachment todevice 500. - In order to provide more flexibility in selecting a suitable implant location for
device 500, a length ofdistal segment 632 of eachtine portion 630 is relatively short compared to that ofdistal segment 232 oftine portion 230, for example, between approximately 0.05 inch and approximately 0.1 inch. The shorter length can help to prevent perforation through the wall of a structure, for example, the heart, at some implant locations, and can reduce a probability for penetratedtine portions 530 to interfere with blood vessels, which interference, for example, may compromise coronary blood supply, as described above. However, with reference back toFIGS. 3A-C , afterdevice 500 is loaded indistal end 310 ofcatheter 300, and opening 313 ofdistal end 310 is positioned in proximity to tissue at a potential implant site, the reduced length oftine portions 530 may hinder initial tine penetration. A sharper terminal end ofdistal segment 532 can solve this problem but may lead to tissue tearing, upon insertion and/or retraction; thus a relatively blunt terminal end ofdistal segment 532 is preferred. So, with further reference toFIG. 10B , eachdistal segment 532 includes atooth 520 and a relativelyblunt end 540, which surroundstooth 520. -
FIG. 10B illustratesend 540 including a pair oflegs 541 and adistal arch 542 that extends betweenlegs 541, distal to tip 522 oftooth 520, for example, being spaced apart therefrom by approximately 0.005 inch. Eachtooth 520 has a length, which is defined from afoot 521 thereof to a tissue-piercingtip 522 thereof, for example, being between approximately 0.025 inch and approximately 0.045 inch, andlegs 541 extend along the length oftooth 520, on opposing sides thereof. Eachtooth 520 andcorresponding end 540 may be laser cut at the same time that tineportions 530 and base portion 503 are cut from the aforementioned tube. - According to the illustrated embodiment,
legs 541 ofend 540 are configured to bend in elastic deformation whendistal arch 542 is pushed against tissue at a potential implant site, for example, as illustrated inFIG. 10C , so thattip 522 oftooth 520, which is configured to resist bending, is exposed to pierce the tissue.FIG. 10C is an enlarged detail view ofdistal segment 532 astine portion 530 is pushed into contact with tissue T at the implant site. With reference back toFIGS. 3A-B , it should be understood that pushingdistal arch 542 against the tissue T may be accomplished, as described above fordevice 200, afterdevice 500 is loaded intodistal end 310 ofcatheter 300 so thathook segments 531 oftine portions 530 are elastically deformed into the open position, at whichdistal segments 532 are directed distally toward opening 313 ofdistal end 310. Aftertip 522 of eachtooth 520 has pierced the tissue, in response to the relatively high push force for initial deployment,legs 541 ofend 540 can relax back into line withtooth 520 so thatdistal arch 542, upon subsequent penetration/insertion oftine portions 530 into tissue, and upon retraction thereof from the tissue, if necessary, preventstip 522 from tearing the tissue. With reference back toFIG. 10B , according to an exemplary embodiment, a thickness t of eachtine portion 530, which is relatively constant along the entire length thereof, is approximately 0.005 inch, a width wf offoot 521 oftooth 520 is between approximately 0.010 inch and approximately 0.015 inch, a width wt oftip 522 oftooth 520 is approximately 0.003 inch, and a width we oflegs 541 anddistal arch 542 is approximately 0.005 inch. -
FIG. 11A is an elevation view of a tissue-penetratingfixation component 83, according to some alternate embodiments of the present invention, which may also be incorporated in the exemplary device ofFIG. 10A .FIG. 11A illustratescomponent 83 including a base portion 803 and a plurality oftine portions 830 extending therefrom, similar tocomponent 53, wherein eachtine portion 830 includes ahook segment 831 and adistal segment 832 that are configured to address both of the aforementioned issues related to tissue penetration and fatigue life.Component 83 may be cut and formed from a Nitinol tube in a manner similar to that described above forcomponent 53.FIG. 10A further illustrates eachhook segment 831 being pre-set to extend along a curvature that encloses angle φ, from aproximal end 81 thereof to adistal end 82 thereof; and eachdistal segment 832 is shown extending along a relatively straight line that is approximately tangent todistal end 82 ofhook segment 831. According to the illustrated embodiment, angle φ is approximately 180 degrees, so that eachdistal segment 832 extends approximately parallel to alongitudinal axis 8 ofcomponent 83. The pre-set curvature ofhook segment 831 is defined by a single radius R, which may be approximately 0.085 inch. -
FIG. 11B is a plan view oftine portion 830, prior to forming the pre-set curvature thereof.FIGS. 11A-B illustrate eachtine portion 830 including a taperedhook portion 831, similar to hookportions tine portions distal end 82 ofhook segment 831, is less than first width W1, in proximity to aproximal end 81 ofhook segment 831.FIGS. 11A-B further illustratedistal segment 832 having a width W3 that is greater than the second width W2.Distal segment 832, likedistal segment 532 ofcomponent 53, includestooth 520 and end 540 to facilitate tissue piercing without tearing, as described above. Likecomponent 53, a thickness t of eachtine portion 830, which is relatively constant along the entire length thereof, may be approximately 0.005 inch, anddistal segment 832 thereof may conform to the aforementioned exemplary dimensions oftooth 520 and end 540. - In the foregoing detailed description, the invention has been described with reference to specific embodiments. However, it may be appreciated that various modifications and changes can be made without departing from the scope of the invention as set forth in the appended claims.
Claims (22)
Priority Applications (6)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US13/955,674 US9155882B2 (en) | 2013-07-31 | 2013-07-31 | Implantable medical devices including tine fixation component having hook segment |
CN201480002158.0A CN104582789B (en) | 2013-07-31 | 2014-07-21 | Fixation for implantable medical device |
EP14748065.1A EP3027267B1 (en) | 2013-07-31 | 2014-07-21 | Fixation for implantable medical devices |
PCT/US2014/047442 WO2015017157A1 (en) | 2013-07-31 | 2014-07-21 | Fixation for implantable medical devices |
US14/831,417 US9579500B2 (en) | 2013-07-31 | 2015-08-20 | Tine fixation components for implantable medical devices |
US14/854,964 US9283381B2 (en) | 2013-07-31 | 2015-09-15 | Fixation for implantable medical devices |
Applications Claiming Priority (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US13/955,674 US9155882B2 (en) | 2013-07-31 | 2013-07-31 | Implantable medical devices including tine fixation component having hook segment |
Related Child Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US14/854,964 Division US9283381B2 (en) | 2013-07-31 | 2015-09-15 | Fixation for implantable medical devices |
Publications (2)
Publication Number | Publication Date |
---|---|
US20150039071A1 true US20150039071A1 (en) | 2015-02-05 |
US9155882B2 US9155882B2 (en) | 2015-10-13 |
Family
ID=51293184
Family Applications (2)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US13/955,674 Active US9155882B2 (en) | 2013-07-31 | 2013-07-31 | Implantable medical devices including tine fixation component having hook segment |
US14/854,964 Active US9283381B2 (en) | 2013-07-31 | 2015-09-15 | Fixation for implantable medical devices |
Family Applications After (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US14/854,964 Active US9283381B2 (en) | 2013-07-31 | 2015-09-15 | Fixation for implantable medical devices |
Country Status (4)
Country | Link |
---|---|
US (2) | US9155882B2 (en) |
EP (1) | EP3027267B1 (en) |
CN (1) | CN104582789B (en) |
WO (1) | WO2015017157A1 (en) |
Cited By (10)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
WO2016183417A1 (en) * | 2015-05-13 | 2016-11-17 | Medtronic, Inc. | Securing an implantable medical device in position while reducing perforations |
WO2017127689A1 (en) * | 2016-01-21 | 2017-07-27 | Medtronic, Inc. | Interventional medical systems |
CN107592821A (en) * | 2015-05-13 | 2018-01-16 | 美敦力公司 | Implanted medical apparatus is secured in place to reduce perforation simultaneously |
US9956400B2 (en) | 2014-10-22 | 2018-05-01 | Cardiac Pacemakers, Inc. | Delivery devices and methods for leadless cardiac devices |
US10099050B2 (en) | 2016-01-21 | 2018-10-16 | Medtronic, Inc. | Interventional medical devices, device systems, and fixation components thereof |
CN109803718A (en) * | 2016-10-06 | 2019-05-24 | 美敦力公司 | Electrode fixuture in insertion type medical system |
US10518084B2 (en) | 2013-07-31 | 2019-12-31 | Medtronic, Inc. | Fixation for implantable medical devices |
US20210046306A1 (en) * | 2019-08-13 | 2021-02-18 | Medtronic, Inc. | Fixation component for multi-electrode implantable medical device |
US11278720B2 (en) | 2014-10-22 | 2022-03-22 | Cardiac Pacemakers, Inc. | Delivery devices and methods for leadless cardiac devices |
US11759632B2 (en) | 2019-03-28 | 2023-09-19 | Medtronic, Inc. | Fixation components for implantable medical devices |
Families Citing this family (106)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US9119959B2 (en) | 2013-07-31 | 2015-09-01 | Medtronic, Inc. | Tine fixation components for implantable medical devices |
US10300286B2 (en) | 2013-09-27 | 2019-05-28 | Medtronic, Inc. | Tools and assemblies thereof for implantable medical devices |
US9526522B2 (en) | 2013-09-27 | 2016-12-27 | Medtronic, Inc. | Interventional medical systems, tools, and assemblies |
EP3308833B1 (en) | 2014-01-10 | 2019-06-26 | Cardiac Pacemakers, Inc. | Methods and systems for improved communication between medical devices |
JP6781044B2 (en) | 2014-01-10 | 2020-11-04 | カーディアック ペースメイカーズ, インコーポレイテッド | System to detect cardiac arrhythmia |
US10478620B2 (en) | 2014-08-26 | 2019-11-19 | Medtronic, Inc. | Interventional medical systems, devices, and methods of use |
US9675798B2 (en) | 2014-08-26 | 2017-06-13 | Medtronic, Inc. | Interventional medical systems, devices, and components thereof |
CN107073275B (en) | 2014-08-28 | 2020-09-01 | 心脏起搏器股份公司 | Medical device with triggered blanking period |
ES2713231T3 (en) | 2015-02-06 | 2019-05-20 | Cardiac Pacemakers Inc | Systems for the safe supply of electrical stimulation therapy |
JP6510660B2 (en) | 2015-02-06 | 2019-05-08 | カーディアック ペースメイカーズ, インコーポレイテッド | System and method for treating cardiac arrhythmias |
US10046167B2 (en) | 2015-02-09 | 2018-08-14 | Cardiac Pacemakers, Inc. | Implantable medical device with radiopaque ID tag |
EP3265172B1 (en) | 2015-03-04 | 2018-12-19 | Cardiac Pacemakers, Inc. | Systems for treating cardiac arrhythmias |
JP6515195B2 (en) | 2015-03-18 | 2019-05-15 | カーディアック ペースメイカーズ, インコーポレイテッド | Implantable medical device and medical system |
US10050700B2 (en) | 2015-03-18 | 2018-08-14 | Cardiac Pacemakers, Inc. | Communications in a medical device system with temporal optimization |
US10350416B2 (en) * | 2015-07-28 | 2019-07-16 | Medtronic, Inc. | Intracardiac pacemaker with sensing extension in pulmonary artery |
US10357159B2 (en) | 2015-08-20 | 2019-07-23 | Cardiac Pacemakers, Inc | Systems and methods for communication between medical devices |
CN108136186B (en) | 2015-08-20 | 2021-09-17 | 心脏起搏器股份公司 | System and method for communication between medical devices |
US9956414B2 (en) | 2015-08-27 | 2018-05-01 | Cardiac Pacemakers, Inc. | Temporal configuration of a motion sensor in an implantable medical device |
US9968787B2 (en) | 2015-08-27 | 2018-05-15 | Cardiac Pacemakers, Inc. | Spatial configuration of a motion sensor in an implantable medical device |
EP3341076B1 (en) | 2015-08-28 | 2022-05-11 | Cardiac Pacemakers, Inc. | Systems and methods for behaviorally responsive signal detection and therapy delivery |
US10226631B2 (en) | 2015-08-28 | 2019-03-12 | Cardiac Pacemakers, Inc. | Systems and methods for infarct detection |
US10159842B2 (en) | 2015-08-28 | 2018-12-25 | Cardiac Pacemakers, Inc. | System and method for detecting tamponade |
WO2017044389A1 (en) | 2015-09-11 | 2017-03-16 | Cardiac Pacemakers, Inc. | Arrhythmia detection and confirmation |
EP3359251B1 (en) | 2015-10-08 | 2019-08-07 | Cardiac Pacemakers, Inc. | Adjusting pacing rates in an implantable medical device |
CN108472490B (en) | 2015-12-17 | 2022-06-28 | 心脏起搏器股份公司 | Conducted communication in a medical device system |
US10905886B2 (en) | 2015-12-28 | 2021-02-02 | Cardiac Pacemakers, Inc. | Implantable medical device for deployment across the atrioventricular septum |
US11006887B2 (en) | 2016-01-14 | 2021-05-18 | Biosense Webster (Israel) Ltd. | Region of interest focal source detection using comparisons of R-S wave magnitudes and LATs of RS complexes |
US10624554B2 (en) * | 2016-01-14 | 2020-04-21 | Biosense Webster (Israel) Ltd. | Non-overlapping loop-type or spline-type catheter to determine activation source direction and activation source type |
WO2017127548A1 (en) | 2016-01-19 | 2017-07-27 | Cardiac Pacemakers, Inc. | Devices for wirelessly recharging a rechargeable battery of an implantable medical device |
WO2017132334A1 (en) | 2016-01-26 | 2017-08-03 | Medtronic, Inc. | Compact implantable medical device and delivery device |
WO2017136548A1 (en) | 2016-02-04 | 2017-08-10 | Cardiac Pacemakers, Inc. | Delivery system with force sensor for leadless cardiac device |
CN108883286B (en) | 2016-03-31 | 2021-12-07 | 心脏起搏器股份公司 | Implantable medical device with rechargeable battery |
US10143823B2 (en) | 2016-04-29 | 2018-12-04 | Medtronic, Inc. | Interventional medical systems and improved assemblies thereof and associated methods of use |
US10668294B2 (en) | 2016-05-10 | 2020-06-02 | Cardiac Pacemakers, Inc. | Leadless cardiac pacemaker configured for over the wire delivery |
US10328272B2 (en) | 2016-05-10 | 2019-06-25 | Cardiac Pacemakers, Inc. | Retrievability for implantable medical devices |
CN109414582B (en) | 2016-06-27 | 2022-10-28 | 心脏起搏器股份公司 | Cardiac therapy system for resynchronization pacing management using subcutaneous sensing of P-waves |
US11207527B2 (en) | 2016-07-06 | 2021-12-28 | Cardiac Pacemakers, Inc. | Method and system for determining an atrial contraction timing fiducial in a leadless cardiac pacemaker system |
US10426962B2 (en) | 2016-07-07 | 2019-10-01 | Cardiac Pacemakers, Inc. | Leadless pacemaker using pressure measurements for pacing capture verification |
EP3487579B1 (en) | 2016-07-20 | 2020-11-25 | Cardiac Pacemakers, Inc. | System for utilizing an atrial contraction timing fiducial in a leadless cardiac pacemaker system |
EP3500342B1 (en) | 2016-08-19 | 2020-05-13 | Cardiac Pacemakers, Inc. | Trans-septal implantable medical device |
WO2018039322A1 (en) | 2016-08-24 | 2018-03-01 | Cardiac Pacemakers, Inc. | Cardiac resynchronization using fusion promotion for timing management |
EP3503799B1 (en) | 2016-08-24 | 2021-06-30 | Cardiac Pacemakers, Inc. | Integrated multi-device cardiac resynchronization therapy using p-wave to pace timing |
CN106362288B (en) * | 2016-09-14 | 2019-06-11 | 郭成军 | Cardiac implant and its fixing means |
US10758737B2 (en) | 2016-09-21 | 2020-09-01 | Cardiac Pacemakers, Inc. | Using sensor data from an intracardially implanted medical device to influence operation of an extracardially implantable cardioverter |
US10994145B2 (en) | 2016-09-21 | 2021-05-04 | Cardiac Pacemakers, Inc. | Implantable cardiac monitor |
US10905889B2 (en) | 2016-09-21 | 2021-02-02 | Cardiac Pacemakers, Inc. | Leadless stimulation device with a housing that houses internal components of the leadless stimulation device and functions as the battery case and a terminal of an internal battery |
WO2018081275A1 (en) | 2016-10-27 | 2018-05-03 | Cardiac Pacemakers, Inc. | Multi-device cardiac resynchronization therapy with timing enhancements |
US10413733B2 (en) | 2016-10-27 | 2019-09-17 | Cardiac Pacemakers, Inc. | Implantable medical device with gyroscope |
EP3532159B1 (en) | 2016-10-27 | 2021-12-22 | Cardiac Pacemakers, Inc. | Implantable medical device delivery system with integrated sensor |
WO2018081017A1 (en) | 2016-10-27 | 2018-05-03 | Cardiac Pacemakers, Inc. | Implantable medical device with pressure sensor |
US10328257B2 (en) * | 2016-10-27 | 2019-06-25 | Medtronic, Inc. | Electrode fixation in interventional medical systems |
EP3532160B1 (en) | 2016-10-27 | 2023-01-25 | Cardiac Pacemakers, Inc. | Separate device in managing the pace pulse energy of a cardiac pacemaker |
US10561330B2 (en) | 2016-10-27 | 2020-02-18 | Cardiac Pacemakers, Inc. | Implantable medical device having a sense channel with performance adjustment |
US10434317B2 (en) | 2016-10-31 | 2019-10-08 | Cardiac Pacemakers, Inc. | Systems and methods for activity level pacing |
CN109890456B (en) | 2016-10-31 | 2023-06-13 | 心脏起搏器股份公司 | System for activity level pacing |
US10583301B2 (en) | 2016-11-08 | 2020-03-10 | Cardiac Pacemakers, Inc. | Implantable medical device for atrial deployment |
EP3538213B1 (en) | 2016-11-09 | 2023-04-12 | Cardiac Pacemakers, Inc. | Systems and devices for setting cardiac pacing pulse parameters for a cardiac pacing device |
WO2018094344A2 (en) | 2016-11-21 | 2018-05-24 | Cardiac Pacemakers, Inc | Leadless cardiac pacemaker with multimode communication |
US10894163B2 (en) | 2016-11-21 | 2021-01-19 | Cardiac Pacemakers, Inc. | LCP based predictive timing for cardiac resynchronization |
EP3541460B1 (en) | 2016-11-21 | 2020-12-23 | Cardiac Pacemakers, Inc. | Delivery devices and wall apposition sensing |
US11198013B2 (en) | 2016-11-21 | 2021-12-14 | Cardiac Pacemakers, Inc. | Catheter and leadless cardiac devices including electrical pathway barrier |
WO2018094342A1 (en) | 2016-11-21 | 2018-05-24 | Cardiac Pacemakers, Inc | Implantable medical device with a magnetically permeable housing and an inductive coil disposed about the housing |
US10639486B2 (en) | 2016-11-21 | 2020-05-05 | Cardiac Pacemakers, Inc. | Implantable medical device with recharge coil |
US10881869B2 (en) | 2016-11-21 | 2021-01-05 | Cardiac Pacemakers, Inc. | Wireless re-charge of an implantable medical device |
US10485981B2 (en) | 2016-12-27 | 2019-11-26 | Cardiac Pacemakers, Inc. | Fixation methods for leadless cardiac devices |
US10894162B2 (en) | 2016-12-27 | 2021-01-19 | Cardiac Pacemakers, Inc. | Delivery devices and methods for leadless cardiac devices |
US10806931B2 (en) | 2016-12-27 | 2020-10-20 | Cardiac Pacemakers, Inc. | Delivery devices and methods for leadless cardiac devices |
EP3562547B1 (en) | 2016-12-27 | 2020-11-18 | Cardiac Pacemakers, Inc. | Leadless delivery catheter with conductive pathway |
US11207532B2 (en) | 2017-01-04 | 2021-12-28 | Cardiac Pacemakers, Inc. | Dynamic sensing updates using postural input in a multiple device cardiac rhythm management system |
EP3573707B1 (en) | 2017-01-26 | 2021-06-16 | Cardiac Pacemakers, Inc. | Delivery devices for leadless cardiac devices |
EP3573708B1 (en) | 2017-01-26 | 2021-03-10 | Cardiac Pacemakers, Inc. | Leadless implantable device with detachable fixation |
EP3573709A1 (en) | 2017-01-26 | 2019-12-04 | Cardiac Pacemakers, Inc. | Leadless device with overmolded components |
US10835753B2 (en) | 2017-01-26 | 2020-11-17 | Cardiac Pacemakers, Inc. | Intra-body device communication with redundant message transmission |
CN110418661B (en) | 2017-03-10 | 2024-01-02 | 心脏起搏器股份公司 | Fixing piece for leadless cardiac device |
US10737092B2 (en) | 2017-03-30 | 2020-08-11 | Cardiac Pacemakers, Inc. | Delivery devices and methods for leadless cardiac devices |
US10905872B2 (en) | 2017-04-03 | 2021-02-02 | Cardiac Pacemakers, Inc. | Implantable medical device with a movable electrode biased toward an extended position |
US10821288B2 (en) | 2017-04-03 | 2020-11-03 | Cardiac Pacemakers, Inc. | Cardiac pacemaker with pacing pulse energy adjustment based on sensed heart rate |
US11577085B2 (en) | 2017-08-03 | 2023-02-14 | Cardiac Pacemakers, Inc. | Delivery devices and methods for leadless cardiac devices |
US10918875B2 (en) | 2017-08-18 | 2021-02-16 | Cardiac Pacemakers, Inc. | Implantable medical device with a flux concentrator and a receiving coil disposed about the flux concentrator |
CN111032148B (en) | 2017-08-18 | 2024-04-02 | 心脏起搏器股份公司 | Implantable medical device with pressure sensor |
US10758733B2 (en) | 2017-09-15 | 2020-09-01 | Medtronic, Inc. | Implantable medical device with retractable fixation sheath |
JP6938778B2 (en) | 2017-09-20 | 2021-09-22 | カーディアック ペースメイカーズ, インコーポレイテッド | Implantable medical device with multiple modes of operation |
US11185703B2 (en) | 2017-11-07 | 2021-11-30 | Cardiac Pacemakers, Inc. | Leadless cardiac pacemaker for bundle of his pacing |
US11071870B2 (en) | 2017-12-01 | 2021-07-27 | Cardiac Pacemakers, Inc. | Methods and systems for detecting atrial contraction timing fiducials and determining a cardiac interval from a ventricularly implanted leadless cardiac pacemaker |
EP3717064B1 (en) | 2017-12-01 | 2023-06-07 | Cardiac Pacemakers, Inc. | Methods and systems for detecting atrial contraction timing fiducials during ventricular filling from a ventricularly implanted leadless cardiac pacemaker |
EP3717060B1 (en) | 2017-12-01 | 2022-10-05 | Cardiac Pacemakers, Inc. | Leadless cardiac pacemaker with reversionary behavior |
WO2019108837A1 (en) | 2017-12-01 | 2019-06-06 | Cardiac Pacemakers, Inc. | Methods and systems for detecting atrial contraction timing fiducials within a search window from a ventricularly implanted leadless cardiac pacemaker |
WO2019136148A1 (en) | 2018-01-04 | 2019-07-11 | Cardiac Pacemakers, Inc. | Dual chamber pacing without beat-to-beat communication |
US11529523B2 (en) | 2018-01-04 | 2022-12-20 | Cardiac Pacemakers, Inc. | Handheld bridge device for providing a communication bridge between an implanted medical device and a smartphone |
US11058880B2 (en) | 2018-03-23 | 2021-07-13 | Medtronic, Inc. | VFA cardiac therapy for tachycardia |
US11235159B2 (en) | 2018-03-23 | 2022-02-01 | Medtronic, Inc. | VFA cardiac resynchronization therapy |
US11400296B2 (en) | 2018-03-23 | 2022-08-02 | Medtronic, Inc. | AV synchronous VfA cardiac therapy |
EP3856331A1 (en) | 2018-09-26 | 2021-08-04 | Medtronic, Inc. | Capture in ventricle-from-atrium cardiac therapy |
US11951313B2 (en) | 2018-11-17 | 2024-04-09 | Medtronic, Inc. | VFA delivery systems and methods |
US11679265B2 (en) | 2019-02-14 | 2023-06-20 | Medtronic, Inc. | Lead-in-lead systems and methods for cardiac therapy |
US11697025B2 (en) | 2019-03-29 | 2023-07-11 | Medtronic, Inc. | Cardiac conduction system capture |
WO2020205401A1 (en) | 2019-03-29 | 2020-10-08 | Cardiac Pacemakers, Inc. | Systems and methods for treating cardiac arrhythmias |
US11446510B2 (en) | 2019-03-29 | 2022-09-20 | Cardiac Pacemakers, Inc. | Systems and methods for treating cardiac arrhythmias |
US11213676B2 (en) | 2019-04-01 | 2022-01-04 | Medtronic, Inc. | Delivery systems for VfA cardiac therapy |
US11712188B2 (en) | 2019-05-07 | 2023-08-01 | Medtronic, Inc. | Posterior left bundle branch engagement |
US11305127B2 (en) | 2019-08-26 | 2022-04-19 | Medtronic Inc. | VfA delivery and implant region detection |
EP4028117B1 (en) | 2019-09-11 | 2024-04-24 | Cardiac Pacemakers, Inc. | Systems for implanting and/or retrieving a leadless cardiac pacing device with helix fixation |
US11510697B2 (en) | 2019-09-11 | 2022-11-29 | Cardiac Pacemakers, Inc. | Tools and systems for implanting and/or retrieving a leadless cardiac pacing device with helix fixation |
US11813466B2 (en) | 2020-01-27 | 2023-11-14 | Medtronic, Inc. | Atrioventricular nodal stimulation |
US11911168B2 (en) | 2020-04-03 | 2024-02-27 | Medtronic, Inc. | Cardiac conduction system therapy benefit determination |
US11813464B2 (en) | 2020-07-31 | 2023-11-14 | Medtronic, Inc. | Cardiac conduction system evaluation |
Family Cites Families (20)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US3814104A (en) | 1971-07-05 | 1974-06-04 | W Irnich | Pacemaker-electrode |
US4103690A (en) | 1977-03-21 | 1978-08-01 | Cordis Corporation | Self-suturing cardiac pacer lead |
DE3529578A1 (en) | 1985-08-17 | 1987-02-19 | Bisping Hans Juergen | IMPLANTABLE ELECTRODE |
US5492119A (en) | 1993-12-22 | 1996-02-20 | Heart Rhythm Technologies, Inc. | Catheter tip stabilizing apparatus |
US5443492A (en) | 1994-02-02 | 1995-08-22 | Medtronic, Inc. | Medical electrical lead and introducer system for implantable pulse generator |
WO2001002053A1 (en) | 1999-07-07 | 2001-01-11 | Cardiac Pacemakers, Inc. | Endocardial electrode assembly having conductive fixation features |
US6684109B1 (en) | 2000-09-13 | 2004-01-27 | Oscor Inc. | Endocardial lead |
US8303511B2 (en) | 2002-09-26 | 2012-11-06 | Pacesetter, Inc. | Implantable pressure transducer system optimized for reduced thrombosis effect |
ATE536201T1 (en) | 2002-09-26 | 2011-12-15 | Pacesetter Inc | CARDIOVASCULAR ANCHORING DEVICE |
US20060247753A1 (en) | 2005-04-29 | 2006-11-02 | Wenger William K | Subcutaneous lead fixation mechanisms |
US7840281B2 (en) | 2006-07-21 | 2010-11-23 | Boston Scientific Scimed, Inc. | Delivery of cardiac stimulation devices |
DE102008040773A1 (en) | 2008-07-28 | 2010-02-04 | Biotronik Crm Patent Ag | Implantable catheter or electrode lead |
US8478431B2 (en) | 2010-04-13 | 2013-07-02 | Medtronic, Inc. | Slidable fixation device for securing a medical implant |
US8532790B2 (en) | 2010-04-13 | 2013-09-10 | Medtronic, Inc. | Slidable fixation device for securing a medical implant |
EP2627406A1 (en) | 2010-10-13 | 2013-08-21 | Nanostim, Inc. | Leadless cardiac pacemaker with anti-unscrewing feature |
US9204842B2 (en) * | 2010-10-29 | 2015-12-08 | Medtronic, Inc. | Medical device fixation attachment mechanism |
US8864676B2 (en) | 2010-10-29 | 2014-10-21 | Medtronic Vascular, Inc. | Implantable medical sensor and fixation system |
US10112045B2 (en) | 2010-12-29 | 2018-10-30 | Medtronic, Inc. | Implantable medical device fixation |
US9775982B2 (en) | 2010-12-29 | 2017-10-03 | Medtronic, Inc. | Implantable medical device fixation |
JP2014516286A (en) | 2011-03-29 | 2014-07-10 | オキュネティクス・インコーポレーテッド | Fasteners, installation systems, and methods for ocular tissue closure and ocular artificial tissue fixation and other uses |
-
2013
- 2013-07-31 US US13/955,674 patent/US9155882B2/en active Active
-
2014
- 2014-07-21 WO PCT/US2014/047442 patent/WO2015017157A1/en active Application Filing
- 2014-07-21 CN CN201480002158.0A patent/CN104582789B/en active Active
- 2014-07-21 EP EP14748065.1A patent/EP3027267B1/en active Active
-
2015
- 2015-09-15 US US14/854,964 patent/US9283381B2/en active Active
Cited By (19)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US11400281B2 (en) | 2013-07-31 | 2022-08-02 | Medtronic, Inc. | Fixation for implantable medical devices |
US10518084B2 (en) | 2013-07-31 | 2019-12-31 | Medtronic, Inc. | Fixation for implantable medical devices |
US10835740B2 (en) | 2014-10-22 | 2020-11-17 | Cardiac Pacemakers, Inc. | Delivery devices and methods for leadless cardiac devices |
US11660446B2 (en) | 2014-10-22 | 2023-05-30 | Cardiac Pacemakers, Inc. | Delivery devices and methods for leadless cardiac devices |
US9956400B2 (en) | 2014-10-22 | 2018-05-01 | Cardiac Pacemakers, Inc. | Delivery devices and methods for leadless cardiac devices |
US11278720B2 (en) | 2014-10-22 | 2022-03-22 | Cardiac Pacemakers, Inc. | Delivery devices and methods for leadless cardiac devices |
CN107592821A (en) * | 2015-05-13 | 2018-01-16 | 美敦力公司 | Implanted medical apparatus is secured in place to reduce perforation simultaneously |
US10143838B2 (en) | 2015-05-13 | 2018-12-04 | Medtronic, Inc. | Securing an implantable medical device in position while reducing perforations |
US10898707B2 (en) | 2015-05-13 | 2021-01-26 | Medtronic, Inc. | Securing an implantable medical device in position while reducing perforations |
WO2016183417A1 (en) * | 2015-05-13 | 2016-11-17 | Medtronic, Inc. | Securing an implantable medical device in position while reducing perforations |
US10463853B2 (en) | 2016-01-21 | 2019-11-05 | Medtronic, Inc. | Interventional medical systems |
US11027125B2 (en) | 2016-01-21 | 2021-06-08 | Medtronic, Inc. | Interventional medical devices, device systems, and fixation components thereof |
CN108883268A (en) * | 2016-01-21 | 2018-11-23 | 美敦力公司 | Intervene medical system |
US10099050B2 (en) | 2016-01-21 | 2018-10-16 | Medtronic, Inc. | Interventional medical devices, device systems, and fixation components thereof |
WO2017127689A1 (en) * | 2016-01-21 | 2017-07-27 | Medtronic, Inc. | Interventional medical systems |
CN109803718A (en) * | 2016-10-06 | 2019-05-24 | 美敦力公司 | Electrode fixuture in insertion type medical system |
US11759632B2 (en) | 2019-03-28 | 2023-09-19 | Medtronic, Inc. | Fixation components for implantable medical devices |
US20210046306A1 (en) * | 2019-08-13 | 2021-02-18 | Medtronic, Inc. | Fixation component for multi-electrode implantable medical device |
US11684776B2 (en) * | 2019-08-13 | 2023-06-27 | Medtronic, Inc. | Fixation component for multi-electrode implantable medical device |
Also Published As
Publication number | Publication date |
---|---|
CN104582789B (en) | 2018-02-23 |
US9283381B2 (en) | 2016-03-15 |
EP3027267B1 (en) | 2017-09-06 |
WO2015017157A1 (en) | 2015-02-05 |
EP3027267A1 (en) | 2016-06-08 |
CN104582789A (en) | 2015-04-29 |
US9155882B2 (en) | 2015-10-13 |
US20160001068A1 (en) | 2016-01-07 |
Similar Documents
Publication | Publication Date | Title |
---|---|---|
US11400281B2 (en) | Fixation for implantable medical devices | |
US9283381B2 (en) | Fixation for implantable medical devices | |
US9987483B2 (en) | Tine fixation components for implantable medical devices | |
CN108883267B (en) | Interventional medical device, device system and fixing assembly thereof | |
CN106659887B (en) | Insertion type medical system, device and its component | |
EP4013490B1 (en) | Fixation component for multi-electrode implantable medical device | |
US20180117307A1 (en) | Electrode fixation in interventional medical systems | |
US7865248B2 (en) | Biasing and fixation features on leads | |
US11065441B2 (en) | Electrode fixation in interventional medical systems | |
US20070239247A1 (en) | Medical electrical lead and delivery system | |
KR102137740B1 (en) | Pacemaker lead for cerclage pacing | |
WO2024115937A1 (en) | Cutting helix for lead fixation |
Legal Events
Date | Code | Title | Description |
---|---|---|---|
AS | Assignment |
Owner name: MEDTRONIC, INC., MINNESOTA Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNORS:GRUBAC, VLADIMIR;KUHN, JONATHAN I;RYS, KENNETH D;SIGNING DATES FROM 20130723 TO 20130730;REEL/FRAME:030915/0552 |
|
FEPP | Fee payment procedure |
Free format text: PAYOR NUMBER ASSIGNED (ORIGINAL EVENT CODE: ASPN); ENTITY STATUS OF PATENT OWNER: LARGE ENTITY |
|
AS | Assignment |
Owner name: MEDTRONIC, INC., MINNESOTA Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNOR:KUHN, JONATHAN L;REEL/FRAME:034579/0739 Effective date: 20141222 |
|
STCF | Information on status: patent grant |
Free format text: PATENTED CASE |
|
MAFP | Maintenance fee payment |
Free format text: PAYMENT OF MAINTENANCE FEE, 4TH YEAR, LARGE ENTITY (ORIGINAL EVENT CODE: M1551); ENTITY STATUS OF PATENT OWNER: LARGE ENTITY Year of fee payment: 4 |
|
MAFP | Maintenance fee payment |
Free format text: PAYMENT OF MAINTENANCE FEE, 8TH YEAR, LARGE ENTITY (ORIGINAL EVENT CODE: M1552); ENTITY STATUS OF PATENT OWNER: LARGE ENTITY Year of fee payment: 8 |